Dark blood balanced steady state free precession imaging

ABSTRACT

Systems, methods, and other embodiments associated with controlling a magnetic resonance imaging (MRI) apparatus to perform a balanced steady state free precession (bSSFP) technique that includes magnetization preparation with differentiated velocity encoding and spoiling residual transverse magnetization are described. The example systems, methods, and other embodiments are also associated with acquiring a dark blood image in response to the bSSFP technique. A dark blood image is one in which NMR signal acquired from an object subjected to the bSSFP technique and magnetization preparation includes NMR signal from flowing spins and NMR signal from non-flowing spins in a desired ratio.

PRIORITY CLAIM

This application claims the benefit of U.S. Provisional Application61/124,726 filed Apr. 18, 2008, titled Dark Blood Balanced Steady StateFree Precession Imaging, by the same inventors.

BACKGROUND

One type of magnetic resonance imaging (MRI) pulse sequence is referredto as balanced steady state free precession (bSSFP) MRI. bSSFP may alsobe referred to as TrueFISP (True Fast Imaging with Steady-statePrecession). MRI involves applying radio frequency (RF) energy to anobject according to carefully crafted pulse sequences in the presence ofa carefully crafted magnetic field. When the object is a human body, theRF energy may be applied to tissues that are not moving (e.g., femur),tissues that are moving (e.g., heart muscle), and to the blood in thebody. Since all of these parts of the body may be excited by the RFenergy, all of these parts may emit nuclear magnetic resonance (NMR)signal from which an image may be reconstructed. While at times it maybe desirable to acquire signal from all these parts, at other times itmay be undesirable.

Flowing blood appears hyperintense in bSSFP magnetic resonance (MR)images. The hyperintense blood may be referred to as “bright blood”. Thehyperintensity may be due, at least in part, to inflowing freshmagnetization, to refocusing of spins that have left an imaging slice.Bright blood may be useful at times. However, bright blood can hindercertain applications. For example, bright blood may hinder examiningblood vessel walls. Bright blood can also cause artifacts in images.These artifacts may compromise image quality, may obscure underlyingpathology, and so on. Thus, some conventional approaches for obtainingdark blood (DB) bSSFP images have been developed. These approachestypically lengthen the repetition time (TR) in a pulse sequence and thuslengthen overall imaging time. This can increase discomfort for apatient, reduce the number of patients that can be seen in a day,increase the likelihood that a patient will move during a scan, and soon. Thus, in general it is desirable to reduce imaging time, not toincrease it. However, in some conventional approaches, TR has beenlengthened to more than 11 ms. This lengthy TR both increases scan timeand exacerbates banding artifacts that may be associated, for example,with accumulated phase.

Conventional TrueFISP is a coherent imaging technique. TrueFISP employsa fully balanced gradient waveform. Image contrast typically dependsprimarily on TR but is determined by T2*/T1 properties (or T2/T1 aroundTE=TR/2). T1 weighting in TrueFISP is impractical due to ever shorteningTR times associated with steady state precession techniques. TrueFISPbuilds on FISP (fast imaging with steady state precession). FISPcombines separately observed signals. But for a missing spoiler gradientpulse and RF spoiling, a FISP sequence is similar to a FLASH (fastlow-angle shot) sequence. Since the spoiler pulse is missing, there maybe transverse magnetization present when the next RF pulse is added tothe steady state. FISP has an alternating sign RF pulse. This may belabeled in pulse sequence diagrams as α and −α (see, for example, FIG.1). This facilitates making image contrast practically independent ofT1.

Diffusion-prepared (DP) bSSFP was proposed for vessel wall imaging. See,for example, Koktzoglou I, Li D. JCMR. 2007, 9(1):33-42. Thediffusion-prepared bSSFP appears to have used a unipolar gradient.Building on this work, in January of 2009, after the priority date ofthis application, Zhaoyang Fan, Debiao Li, et al described 3D peripheralsubtraction MRA using flow-spoiled ECG-triggered balanced SSFP, inJournal of Cardiovascular Magnetic Resonance 2009, 11(Suppl 1):P288,doi:10.1186/1532-429X-11-S1-P288. In the January 2009 technique, theKoktzoglou DP module was modified by using bipolar gradient rather thanunipolar gradient. The bipolar gradient was applied both before andafter a central 180 degree RF pulse to address artifacts resulting froman imperfect frequency response. FIG. 11 illustrates the Fan-Li, et almodified flow-sensitizing dephasing (FSD) preparation. Note thatspoiling only occurs once per FSD preparation, after the −90°_(x) pulse.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of the specification, illustrate various example systems, methods,and other example embodiments of various aspects of the invention. Itwill be appreciated that the illustrated element boundaries (e.g.,boxes, groups of boxes, or other shapes) in the figures represent oneexample of the boundaries. One of ordinary skill in the art willappreciate that in some examples one element may be designed as multipleelements or that multiple elements may be designed as one element. Insome examples, an element shown as an internal component of anotherelement may be implemented as an external component and vice versa.Furthermore, elements may not be drawn to scale.

FIG. 1 illustrates one example TR of a dark blood (DB) bSSFP (DBbSSFP)sequence.

FIG. 2 illustrates an example non-refocused velocity encoding schemeassociated with a DBbSSFP sequence.

FIG. 3 illustrates an example refocused velocity encoding schemeassociated with a DBbSSFP sequence.

FIG. 4 illustrates an example method associated with DBbSSFP MRI usingmagnetization prepared differentiated velocity encoding.

FIG. 5 illustrates an MRI apparatus associated with suppressing signalfrom flowing spins in a short TR bSSFP sequence.

FIG. 6 illustrates an example method associated with DBbSSFP MRI usingmagnetization prepared differentiated velocity encoding and a spoilinggradient pulse.

FIG. 7 illustrates an example method associated with DBbSSFP MRI usingmagnetization prepared differentiated velocity encoding and a spoilinggradient pulse.

FIG. 8 illustrates an example apparatus associated with DBbSSFP MRIusing magnetization prepared differentiated velocity encoding and aspoiling gradient pulse.

FIG. 9 illustrates an example apparatus associated with DBbSSFP MRIusing magnetization prepared differentiated velocity encoding and aspoiling gradient pulse.

FIG. 10 illustrates an example conventional TrueFISP pulse sequence.

FIG. 11 illustrates an FSD preparation module.

DETAILED DESCRIPTION

Example systems and methods provide dark blood balanced steady statefree precession (DBbSSFP) magnetic resonance imaging (MRI). Examplesystems and methods adapt conventional steady state free precession(e.g., TrueFISP) by preparing magnetization by periodically applyingbipolar velocity encoding gradients on different axes and by spoilingresidual transverse magnetization. In one example, bSSFP magnetizationis periodically stored along the z-axis using an α/2 pulse.

Recall that conventional TrueFISP is a coherent imaging technique thatemploys a fully balanced gradient waveform. Recall also that TrueFISPbuilds on FISP, which combined separately observed signals but wasmissing a spoiler pulse that led to transverse magnetization beingpresent when the next RF pulse is added to the steady state. An exampleconventional TrueFISP pulse sequence 1000 is provided in FIG. 10. Notethat there is no spoiling pulse. Example systems and methods spoiltransverse magnetization and perform black blood preparation. Comparingthe pulse sequence 1000 in FIG. 10 with the pulse sequence 100 in FIG. 1illustrates differences between a conventional TrueFISP sequence and aDBbSSFP sequence. Comparing the pulse sequence 1100 in FIG. 11 with thepulse sequence 100 in FIG. 1 illustrates differences between one attemptat flow-sensitizing dephasing-prepared (FSD) bSSFP and the approachdescribed herein.

FIG. 1 illustrates an example dark blood bSSFP sequence 100. One skilledin the art will recognize the portions of sequence 100 that fall withinregion 130. These include both positive and negative α and α/2 pulses.In addition to the bSSFP portions that fall within region 130, thesequence 100 also includes black blood preparation (BBP) at 110 andspoiling gradient pulses at 120 and 140. The BBP at 110 may include, forexample, periodically applying bipolar velocity encoding gradients ondifferent axes. In one example, the BBP at 110 may include non-refocusedvelocity encoding as demonstrated in FIG. 2. The non-refocused velocityencoding is performed between a ninety degree pulse 210 associated withthe x axis and a −90 degree pulse 220 associated with the x axis. Whileplus and minus 90 degree pulses associated with the x axis areillustrated, one skilled in the art will appreciate that other pulsesmay be employed. Thus, FIG. 2 illustrates pulses that would be appliedduring BBP 110 in FIG. 1. Note that x, y, and z axes may be used in thenon-refocused velocity encoding.

In another example, the BBP at 110 may include refocused velocityencoding as demonstrated in FIG. 3. The refocused velocity encoding isperformed between a ninety degree pulse 310 associated with the x axisand a −90 degree pulse 320 associated with the x axis. The refocusedvelocity encoding also includes a middle 180 degree pulse 330 associatedwith the y axis. While plus and minus 90 degree pulses associated withthe x axis are illustrated, and while a 180 degree pulse 330 associatedwith the y axis are illustrated, one skilled in the art will appreciatethat other pulses may be employed. Thus, FIG. 3 illustrates pulses thatwould be applied during BBP 110 in FIG. 1. Note again that x, y, and zaxes may be used in the refocused velocity encoding.

In one example, applied velocity encoding associated with BBP at 110imparts phase in proportion to the velocity of flowing spins.Differentiating the amount of velocity encoding suppresses differentflow velocities. This facilitates improving image quality under avariety of conditions. For example, flow suppression may be provided atdifferent velocity ranges. In one example, flow suppression may beprovided for velocity (V) up to 125 cm/s. Flow suppression refers tolimiting undesired NMR signal from flowing spins. Thus, in a dark bloodtechnique, NMR signal from spins in flowing blood are suppressed.

Flow suppression may be provided for both on-resonance and off-resonanceconditions. In one embodiment, example systems and methods may provideflow suppression of at least 50% for π radians off-resonance. In anotherembodiment, example systems and methods may provide flow suppression ofat least 90% for π radians off-resonance. In another embodiment, examplesystems and methods may provide flow suppression of at least 99% for πradians off-resonance. In one embodiment, example systems and methodsmay provide flow suppression of at least 50% for π radians on-resonant.In another embodiment, example systems and methods may provide flowsuppression of at least 90% for π radians on-resonant. In anotherembodiment, example systems and methods may provide flow suppression ofat least 95% for π radians on-resonant. In one embodiment, examplesystems and methods may provide average flow suppression of at least 50%over all de-phasing angles. In another embodiment, example systems andmethods may provide average flow suppression of at least 90% over allde-phasing angles. In another embodiment, example systems and methodsmay provide average flow suppression of at least 95% over all de-phasingangles.

The sequence 100 also includes spoiling residual transversemagnetization at 120 and 140. The spoiler gradients at 120 eliminate thesignal from flowing blood remaining in the transverse plane after the−90°_(x) magnetization preparation pulse (due to the phase accumulatedby the flowing spins during the velocity encoding gradients). Thespoiler gradients at 140 eliminate any residual magnetization in thetransverse plane after the α/2 storage pulse. Removing the residualtransverse magnetization improves DBbSSFP by suppressing the flow signaland preventing imaging artifacts; therefore example DBbSSFP MRI spoilsthat residual transverse magnetization at 120 and 140. One skilled inthe art will understand that residual transverse magnetization may bespoiled in different ways.

Thus, example systems and methods suppress signal from flowing spins ina short TR DBbSSFP sequence. The flowing spins would be associated, forexample, with blood flowing through a blood vessel, with blood flowinginto and out of an organ, and so on. Example systems and methods reduceT2 decay dependant signal loss in stationary spins during velocityencoding. The stationary spins would be those associated with, forexample, a blood vessel wall while the flowing spins would be thoseassociated with, for example, blood flowing through that blood vessel.Recall that bSSFP contrast is primarily associated with T2*/T1, and notT1. Therefore, reducing T2 decay dependant signal loss in stationaryspins enhances the ability to retrieve and process meaningful signalfrom those stationary spins. Example systems and methods provideperiodic magnetization preparation with differentiated velocity encodingto produce this enhancement. This combination leads to suppressing boththrough plane and in plane blood flow in TrueFISP. The Differentiatedvelocity encoding may include progressively reducing the magnitude offlow signal after DB preparations. In order to do this for a range offlow velocities it is necessary to vary the gradient first moment andthus the flow signal phase after the velocity encoding gradient. In oneembodiment, this involves randomly varying the gradient first momentover a specified range. In another embodiment, non-random ways to varythe first moment of the gradient to improve the flow spoilingcharacteristics may be employed.

The following includes definitions of selected terms employed herein.The definitions include various examples and/or forms of components thatfall within the scope of a term and that may be used for implementation.The examples are not intended to be limiting. Both singular and pluralforms of terms may be within the definitions.

References to “one embodiment”, “an embodiment”, “one example”, “anexample”, and so on, indicate that the embodiment(s) or example(s) sodescribed may include a particular feature, structure, characteristic,property, element, or limitation, but that not every embodiment orexample necessarily includes that particular feature, structure,characteristic, property, element or limitation. Furthermore, repeateduse of the phrase “in one embodiment” does not necessarily refer to thesame embodiment, though it may.

“Computer-readable medium”, as used herein, refers to a medium thatstores signals, instructions and/or data. A computer-readable medium maytake forms, including, but not limited to, non-volatile media, andvolatile media. Non-volatile media may include, for example, opticaldisks, magnetic disks, and so on. Volatile media may include, forexample, semiconductor memories, dynamic memory, and so on. Common formsof a computer-readable medium may include, but are not limited to, afloppy disk, a flexible disk, a hard disk, a magnetic tape, othermagnetic medium, an ASIC, a CD, other optical medium, a RAM, a ROM, amemory chip or card, a memory stick, and other media from which acomputer, a processor or other electronic device can read.

“Logic”, as used herein, includes but is not limited to hardware,firmware, software in execution on a machine, and/or combinations ofeach to perform a function(s) or an action(s), and/or to cause afunction or action from another logic, method, and/or system. Logic mayinclude a software controlled microprocessor, a discrete logic (e.g.,ASIC), an analog circuit, a digital circuit, a programmed logic device,a memory device containing instructions, and so on. Logic may includeone or more gates, combinations of gates, or other circuit components.Where multiple logical logics are described, it may be possible toincorporate the multiple logical logics into one physical logic.Similarly, where a single logical logic is described, it may be possibleto distribute that single logical logic between multiple physicallogics.

An “operable connection”, or a connection by which entities are“operably connected”, is one in which signals, physical communications,and/or logical communications may be sent and/or received. An operableconnection may include a physical interface, an electrical interface,and/or a data interface. An operable connection may include differingcombinations of interfaces and/or connections sufficient to allowoperable control. For example, two entities can be operably connected tocommunicate signals to each other directly or through one or moreintermediate entities (e.g., processor, operating system, logic,software). Logical and/or physical communication channels can be used tocreate an operable connection.

“Signal”, as used herein, includes but is not limited to, electricalsignals, optical signals, analog signals, digital signals, data,computer instructions, processor instructions, messages, a bit, a bitstream, or other means that can be received, transmitted and/ordetected.

“User”, as used herein, includes but is not limited to one or morepersons, software, computers or other devices, or combinations of these.

Some portions of the detailed descriptions that follow are presented interms of algorithms and symbolic representations of operations on databits within a memory. These algorithmic descriptions and representationsare used by those skilled in the art to convey the substance of theirwork to others. An algorithm, here and generally, is conceived to be asequence of operations that produce a result. The operations may includephysical manipulations of physical quantities. Usually, though notnecessarily, the physical quantities take the form of electrical ormagnetic signals capable of being stored, transferred, combined,compared, and otherwise manipulated in a logic, and so on. The physicalmanipulations create a concrete, tangible, useful, real-world result.

It has proven convenient at times, principally for reasons of commonusage, to refer to these signals as bits, values, elements, symbols,characters, terms, numbers, and so on. It should be borne in mind,however, that these and similar terms are to be associated with theappropriate physical quantities and are merely convenient labels appliedto these quantities. Unless specifically stated otherwise, it isappreciated that throughout the description, terms including processing,computing, determining, and so on, refer to actions and processes of acomputer system, logic, processor, or similar electronic device thatmanipulates and transforms data represented as physical (electronic)quantities.

Example methods may be better appreciated with reference to flowdiagrams. While for purposes of simplicity of explanation, theillustrated methodologies are shown and described as a series of blocks,it is to be appreciated that the methodologies are not limited by theorder of the blocks, as some blocks can occur in different orders and/orconcurrently with other blocks from that shown and described. Moreover,less than all the illustrated blocks may be required to implement anexample methodology. Blocks may be combined or separated into multiplecomponents. Furthermore, additional and/or alternative methodologies canemploy additional, not illustrated blocks.

FIG. 4 illustrates a method 400 associated with DBbSSFP. Method 400includes, at 410, controlling an MR apparatus to perform a DBbSSFPimaging technique that includes a black blood preparation phase. Indifferent examples the black blood preparation phase includesnon-refocused velocity encoding or refocused velocity encoding. In oneexample, the TR associated with a DBbSSFP pulse sequence is less than 11ms. In another example the TR associated with a DBbSSFP pulse sequenceis less than 8 ms.

Method 400 also includes, at 420, acquiring a dark blood image inresponse to the DBbSSFP imaging technique controlled at 410. The DBbSSFPimaging technique provides flow suppression at a velocity of up to 125cm/s and may provide configurable flow suppression. In one example, theDBbSSFP imaging technique provides at least 90% flow suppression for πradians off-resonance, provides at least 90% flow suppression for πradians on-resonant, and provides an average 90% flow suppression overall dephasing angles. Additionally, the DBbSSFP imaging techniqueprovides 20% reduction of on-resonance spin signal for stationary spins.

In one example, method 400 may be a computer-implemented method. Method400 may include, at 410, controlling an MRI apparatus to apply magneticfields and/or RF pulses to an object to be imaged. The magnetic fieldsand RF pulses are configured to produce dark blood balanced steady statefree precession (DBbSSFP) magnetic resonance imaging (MRI). Some of theRF and gradient pulses are organized into a magnetization preparationwith differentiated velocity encoding module and other RF and/orgradient pulses are organized into a residual transverse magnetizationspoiling module. The controlling at 410 may include controlling the MRIapparatus to periodically store bSSFP magnetization along the z-axisusing an α/2 pulse.

Method 400 also includes, at 420, controlling the MRI apparatus toacquire an image in response to the DBbSSFP imaging. The object to beimaged by method 400 may include both flowing spins and non-flowingspins. Therefore, that NMR signal received from the object to be imagedmay include NMR signal from flowing spins and NMR signal fromnon-flowing spins. Therefore, the magnetic fields and RF pulses areconfigured to yield a situation where the NMR signal from flowing spinsappears in a desired ratio with respect to NMR signal from non-flowingspins.

The desired ratio may be satisfied under different conditions. In oneexample, the desired ratio is satisfied when at least 90% of NMR signalfrom flowing spins for π radians off-resonance is suppressed. In anotherexample, the desired ratio is satisfied when at least 90% of NMR signalfrom flowing spins for π radians on-resonant is suppressed. In yetanother example, the desired ratio is satisfied when on average 90% ofNMR signal from flowing spins over all de-phasing angles is suppressed.

In one example, controlling the MRI apparatus to perform themagnetization preparation with differentiated velocity encoding phasecomprises controlling the MRI apparatus to periodically apply bipolarvelocity encoding gradients on different axes. The differentiatedvelocity encoding may be performed in different manners. In one example,the differentiated velocity encoding is non-refocused velocity encoding,while in another example, the differentiated velocity encoding isrefocused velocity encoding. The velocity encoding may be proportionalto velocity. Therefore, in one example, controlling the MRI apparatus toperform the magnetization preparation with differentiated velocityencoding phase may include controlling the MRI apparatus to apply phaseencoding pulses configured to impart phase in proportion to the velocityof the flowing spins. The flowing spins may be moving up to 125 cm/s insome examples.

In one example, controlling the MRI apparatus at 410 to perform theresidual transverse magnetization spoiling phase includes controllingthe MRI apparatus to apply, per TR, a first spoiling gradient pulsebefore bSSFP pulses in the TR and a second spoiling gradient pulse afterbSSFP pulses in the TR.

While FIG. 4 illustrates various actions occurring in serial, it is tobe appreciated that various actions illustrated in FIG. 4 could occursubstantially in parallel. By way of illustration, a first process couldcontrol an MR apparatus to produce DBbSSFP pulse sequences and a secondprocess could acquire NMR signal associated with producing a DB image inresponse to the DBbSSFP sequences. While two processes are described, itis to be appreciated that a greater and/or lesser number of processescould be employed and that lightweight processes, regular processes,threads, and other approaches could be employed.

FIG. 5 illustrates an example MRI apparatus 500 configured with aDBbSSFP control logic 599 to facilitate controlling MRI apparatus 500 toperform a DBbSSFP imaging technique that includes dark blood preparationand spoiling residual transverse magnetization. The dark bloodpreparation may include, for example, non-refocused velocity encoding,focused velocity encoding, and so on. Thus, MRI apparatus 500 providesmeans to acquire an MR image that depends, at least in part, on aDBbSSFP imaging scheme that includes magnetization prepareddifferentiated velocity encoding.

The apparatus 500 includes a basic field magnet(s) 510 and a basic fieldmagnet supply 520. Ideally, the basic field magnets 510 would produce auniform B₀ field. However, in practice, the B₀ field may not be uniform,and may vary over an object being imaged by the MRI apparatus 500. MRIapparatus 500 may include gradient coils 530 configured to emit gradientmagnetic fields like G_(S), G_(P) and G_(R). The gradient coils 530 maybe controlled, at least in part, by a gradient coils supply 540. In someexamples, the timing, strength, and orientation of the gradient magneticfields may be controlled, and thus selectively adapted during an MRIprocedure.

MRI apparatus 500 may include a set of RF antennas 550 that areconfigured to generate RF pulses and to receive resulting magneticresonance signals from an object to which the RF pulses are directed. Insome examples, how the pulses are generated and how the resulting MRsignals are received may be controlled and thus may be selectivelyadapted during an MRI procedure. Separate RF transmission and receptioncoils can be employed. The RF antennas 550 may be controlled, at leastin part, by a set of RF transmission units 560. An RF transmission unit560 may provide a signal to an RF antenna 550.

The gradient coils supply 540 and the RF transmission units 560 may becontrolled, at least in part, by a control computer 570. The magneticresonance signals received from the RF antennas 550 can be employed togenerate an image and thus may be subject to a transformation processlike a two dimensional FFT that generates pixilated image data. Thetransformation can be performed by an image computer 580 or othersimilar processing device. The image data may then be shown on a display590. While FIG. 5 illustrates an example MRI apparatus 500 that includesvarious components connected in various ways, it is to be appreciatedthat other MRI apparatus may include other components connected in otherways.

FIG. 6 illustrates an example method 600. Method 600 is associated withDBbSSFP MRI using magnetization prepared differentiated velocityencoding and a spoiling gradient pulse. Method 600 includes, at 610,controlling an MRI apparatus to produce a bSSFP sequence. The bSSFPsequence is to be applied to an object having flowing spins andnon-flowing spins. The flowing spins may include through plane flowingspins and in plane flowing spins.

Method 600 also includes, at 620, controlling the MRI apparatus toperform differentiated velocity encoding based periodic magnetizationpreparation in association with the bSSFP sequence. The velocityencoding based periodic magnetization preparation may be similar to thatdescribed elsewhere herein.

Method 600 also includes, at 630, controlling the MRI apparatus toperform residual transverse magnetization spoiling in association withthe bSSFP sequence. The residual transverse magnetization spoiling mayalso be similar to that described elsewhere herein.

Method 600 also includes, at 640, acquiring an NMR signal from theobject. Since the object has both flowing spins and non-flowing spins,NMR signal from the object may include NMR signal from the flowing spinsand NMR signal from the non-flowing spins. Due to the careful craftingof the magnetic fields and RF pulses associated with the DBbSSFP pulsesequence, the NMR signal from flowing spins appears in a desired ratiowith respect to NMR signal from non-flowing spins. In one example thedesired ratio is achieved when at least 95% of the NMR signal isattributable to non-flowing spins and less than 5% of the NMR signal isattributable to flowing spins.

FIG. 7 illustrates another embodiment of method 600. This embodiment ofmethod 600 includes a calibration phase. At 650, a determination is madeconcerning whether the desired suppression ratio has been satisfied. Ifthe determination at 650 is Yes, then method 600 can conclude. If thedetermination at 650 is No, then method 600 may include, at 660,selectively modifying the differentiated velocity encoding basedperiodic magnetization preparation or the transverse magnetizationspoiling. Method 600 may return to 610 to acquire a DB image with bettersuppression.

FIG. 8 illustrates an apparatus 800. Apparatus 800 is associated withDBbSSFP MRI using magnetization prepared differentiated velocityencoding and a spoiling gradient pulse. Apparatus 800 includes a pulsesequence logic 810. Pulse sequence logic 810 is configured to apply abSSFP pulse sequence to an object having flowing spins and non-flowingspins. An example pulse sequence is provided in FIG. 1. The flowingspins may include through plane flowing spins and in plane flowingspins.

Apparatus 800 also includes a periodic magnetization preparation logic820. Preparation logic 820 is configured to perform differentiatedvelocity encoding by periodically applying bipolar velocity encodinggradients on different axes. The differentiated velocity encoding may berefocused or non-refocused velocity encoding as illustrated in FIGS. 2and 3. In one example, the periodic magnetization preparation logic 820is configured to apply phase encoding pulses configured to impart phasein proportion to the velocity of the flowing spins. The object to beimaged may include spins flowing at up to 125 cm/s.

Apparatus 800 also includes a transverse magnetization spoiling logic830. Spoiling logic 830 is configured to mitigate residual transversemagnetization produced as a result of the bSSFP pulse sequence.Apparatus 800 also includes an acquisition logic 840. Acquisition logic840 is configured to acquire an NMR signal from the object in responseto the bSSFP pulse sequence, the differentiated velocity encoding, andthe transverse magnetization mitigation. The NMR signal may include NMRsignal from flowing spins and NMR signal from non-flowing spins. Thepulse sequence logic 810, the periodic magnetization preparation logic820, and the transverse magnetization spoiling logic 830 are configuredto produce conditions in the object to be image so that NMR signal fromflowing spins appears in a desired ratio with respect to NMR signal fromnon-flowing spins. In one example, the desired ratio requires at least90% suppression of NMR signal from flowing spins for π radiansoff-resonance, at least 90% suppression of NMR signal from flowing spinsfor π radians on-resonant, and an average 90% suppression of NMR signalfrom flowing spins over all de-phasing angles.

FIG. 9 illustrates another embodiment of apparatus 800. This embodimentof apparatus 800 includes a calibration logic 850. Calibration logic 850is configured to selectively modify the differentiated velocity encodingbased periodic magnetization preparation or the transverse magnetizationspoiling in response to determining that NMR signal from flowing spinsin the object does not appear in the desired ratio with respect to NMRsignal from non-flowing spins in the object. For example, calibrationlogic 850 may switch the differentiated velocity encoding from focusedto non-refocused, may change the amplitude of a spoiling gradient pulse,and so on.

While example systems, methods, and so on have been illustrated bydescribing examples, and while the examples have been described inconsiderable detail, it is not the intention of the applicants torestrict or in any way limit the scope of the appended claims to suchdetail. It is, of course, not possible to describe every conceivablecombination of components or methodologies for purposes of describingthe systems, methods, and so on described herein. Therefore, theinvention is not limited to the specific details, the representativeapparatus, and illustrative examples shown and described. Thus, thisapplication is intended to embrace alterations, modifications, andvariations that fall within the scope of the appended claims.

To the extent that the term “includes” or “including” is employed in thedetailed description or the claims, it is intended to be inclusive in amanner similar to the term “comprising” as that term is interpreted whenemployed as a transitional word in a claim.

To the extent that the term “or” is employed in the detailed descriptionor claims (e.g., A or B) it is intended to mean “A or B or both”. Whenthe applicants intend to indicate “only A or B but not both” then theterm “only A or B but not both” will be employed. Thus, use of the term“or” herein is the inclusive, and not the exclusive use. See, Bryan A.Garner, A Dictionary of Modern Legal Usage 624 (2d. Ed. 1995).

To the extent that the phrase “one or more of, A, B, and C” is employedherein, (e.g., a data store configured to store one or more of, A, B,and C) it is intended to convey the set of possibilities A, B, C, AB,AC, BC, and/or ABC (e.g., the data store may store only A, only B, onlyC, A&B, A&C, B&C, and/or A&B&C). It is not intended to require one of A,one of B, and one of C. When the applicants intend to indicate “at leastone of A, at least one of B, and at least one of C”, then the phrasing“at least one of A, at least one of B, and at least one of C” will beemployed.

1. A computer-implemented method, comprising: controlling a magneticresonance imaging (MRI) apparatus to apply, to an object to be imaged,one or more of, magnetic fields, and radio frequency (RF) pulses, wherethe magnetic fields and RF pulses are associated with dark bloodbalanced steady state free precession (DBbSSFP) magnetic resonanceimaging (MRI), where the object to be imaged comprises flowing spins andnon-flowing spins, and where RF pulses are organized into amagnetization preparation with differentiated velocity encoding phaseand a residual transverse magnetization spoiling phase; and controllingthe MRI apparatus to acquire an image in response to the DBbSSFPimaging, where nuclear magnetic resonance (NMR) signal received from theobject to be imaged includes NMR signal from flowing spins and NMRsignal from non-flowing spins, where the NMR signal from flowing spinsappears in a desired ratio with respect to NMR signal from non-flowingspins.
 2. The computer-implemented method of claim 1, comprisingcontrolling the MRI apparatus to periodically store bSSFP magnetizationalong the z-axis using an α/2 pulse.
 3. The computer-implemented methodof claim 1, where controlling the MRI apparatus to perform themagnetization preparation with differentiated velocity encoding phasecomprises controlling the MRI apparatus to periodically apply bipolarvelocity encoding gradients on different axes.
 4. Thecomputer-implemented method of claim 3, where the differentiatedvelocity encoding is non-refocused velocity encoding.
 5. Thecomputer-implemented method of claim 3, where the differentiatedvelocity encoding is refocused velocity encoding.
 6. Thecomputer-implemented method of claim 3, where controlling the MRIapparatus to perform the magnetization preparation with differentiatedvelocity encoding phase comprises controlling the MRI apparatus to applyphase encoding pulses configured to impart phase in proportion to thevelocity of the flowing spins.
 7. The computer-implemented method ofclaim 3, where a TR associated with a DBbSSFP pulse sequence is lessthan 11 ms.
 8. The computer-implemented method of claim 3, where theobject to be imaged includes flowing spins flowing at up to 125 cm/s. 9.The computer-implemented method of claim 3, where the desired ratio issatisfied when at least 90% of NMR signal from flowing spins for πradians off-resonance is suppressed.
 10. The computer-implemented methodof claim 3, where the desired ratio is satisfied when at least 90% ofNMR signal from flowing spins for π radians on-resonant is suppressed.11. The computer-implemented method of claim 3, where the desired ratiois satisfied when on average 90% of NMR signal from flowing spins overall de-phasing angles is suppressed.
 12. The computer-implemented methodof claim 3, where controlling the MRI apparatus to perform the residualtransverse magnetization spoiling phase comprises controlling the MRIapparatus to apply, per TR, a first spoiling gradient pulse before bSSFPpulses in the TR and a second spoiling gradient pulse after bSSFP pulsesin the TR.
 13. The computer-implemented method of claim 1, where theobject to be imaged includes in plane flowing spins and through planeflowing spins, where the desired ratio is maintained for in planeflowing spins, and where the desired ratio is maintained for throughplane flowing spins.
 14. A computer-readable medium storingcomputer-executable instructions that when executed by a computer causethe computer to perform a method, the method comprising: controlling anMRI apparatus to produce a bSSFP sequence, where the bSSFP sequence isto be applied to an object having flowing spins and non-flowing spins,where the flowing spins include through plane flowing spins and in planeflowing spins; controlling the MRI apparatus to perform differentiatedvelocity encoding based periodic magnetization preparation inassociation with the bSSFP sequence; controlling the MRI apparatus toperform residual transverse magnetization spoiling in association withthe bSSFP sequence; and acquiring an NMR signal from the object, wherethe NMR signal includes NMR signal from flowing spins and NMR signalfrom non-flowing spins, where the NMR signal from flowing spins appearsin a desired ratio with respect to NMR signal from non-flowing spins.15. The computer-readable medium of claim 14, where the TR for the bSSFPsequence is less than 11 ms.
 16. The computer-readable medium of claim15, where the desired ratio is achieved when at least 95% of the NMRsignal is attributable to non-flowing spins and less than 5% of the NMRsignal is attributable to flowing spins.
 17. The computer-readablemedium of claim 16, where the differentiated velocity encoding isnon-refocused velocity encoding.
 18. The computer-readable medium ofclaim 17, the method comprising: in response to acquiring the NMR signalfrom the object and determining that NMR signal from flowing spins doesnot appear in a desired ratio with respect to NMR signal fromnon-flowing spins, selectively modifying one or more of, thedifferentiated velocity encoding based periodic magnetizationpreparation, and the transverse magnetization spoiling.